US3839204A - Integral blood heat and component exchange device and two flow path membrane blood gas exchanger - Google Patents

Integral blood heat and component exchange device and two flow path membrane blood gas exchanger Download PDF

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US3839204A
US3839204A US00247987A US24798772A US3839204A US 3839204 A US3839204 A US 3839204A US 00247987 A US00247987 A US 00247987A US 24798772 A US24798772 A US 24798772A US 3839204 A US3839204 A US 3839204A
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blood
gas
exchanger
membrane
frame
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US00247987A
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D Ingenito
W Mathewson
D Ryon
G Walmet
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General Electric Co
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General Electric Co
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Priority to US00247987A priority Critical patent/US3839204A/en
Priority to CA159,496A priority patent/CA1002844A/en
Priority to SE7305569A priority patent/SE405681B/xx
Priority to JP48046275A priority patent/JPS4942188A/ja
Priority to DE2321131A priority patent/DE2321131A1/de
Priority to GB265776A priority patent/GB1437634A/en
Priority to GB2004573A priority patent/GB1437633A/en
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    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D61/00—Processes of separation using semi-permeable membranes, e.g. dialysis, osmosis or ultrafiltration; Apparatus, accessories or auxiliary operations specially adapted therefor
    • B01D61/24—Dialysis ; Membrane extraction
    • B01D61/28—Apparatus therefor
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D63/00—Apparatus in general for separation processes using semi-permeable membranes
    • B01D63/08—Flat membrane modules
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D2313/00—Details relating to membrane modules or apparatus
    • B01D2313/22—Cooling or heating elements
    • B01D2313/221—Heat exchangers
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D2325/00—Details relating to properties of membranes
    • B01D2325/08—Patterned membranes

Definitions

  • a device for oxygenating or dialyzing blood has elementary units comprising a heat exchanger closecoupled to a component exchanger comprising one or more frames having rectangular openings and a gas permeable membrane on each face.
  • heat exchanger element heat is transferred via conduction from a source or to a sink through a membrane to or from a flowing film of blood.
  • Two confronting membranes define a thin passageway for blood in the component exchanger element and remote sides of the membranes confront a second passageway in which another fluid such as dialysate or oxygen enriched gas flows, the passageway containing an open support structure.
  • the support structure distributes the gas uniformly and supports the membranes when the space between them is pressurized with blood.
  • thermoplastically formed protuberances project integrally from the membranes into the blood space for precisely defining the blood film thickness.
  • a blood component exchanger including an open support structure shaped to provide two path thin film flows therethrough.
  • the present invention relates to devices for transferring heat and gaseous or other components through membranes into and out of fluids. More particularly, it is concerned with liquid-liquid or gas-liquid transfer devices, and such devices which incorporate an integral heat exchanger. These devices find utility as blood dialyzers, e.g., in artificial kidneys, and as blood oxygenators, e.g., in artificial lungs.
  • Membrane-type blood gas diffusing devices developed up to this time exhibit reduced blood trauma and improved gas exchange efficiency compared with a film-type or bubble-type device.
  • the prior art membrane-types usually comprise stacked membrane envelopes with blood running on one side of the membrane and gas on the other side. Two such devices are described in Lande, et al, U.S. Pat. No. 3,396,849, and by Bramson, et al, in J. Thorac. Cardiov. Surg. 50, 391 (1965). Separators with intricate channels are used to simulate capillary flow and supposedly to minimize the formation of rivulets or preferential flow paths which militate against blood in the device being efficiently in contact with the membrane surfaces. These prior devices have been unduly large for their gas exchange capacity.
  • the membrane device of the said copending application is characterized by thin plastic frames each having a gas permeable membrane adhered to one of its faces.
  • the frames are stacked in pairs with their membrane covered surfaces confronting each other to form a blood envelope, having a thin, large area path for a blood film to flow between membranes.
  • the blood remote sides of the envelopes are recessed in an amount slightly less than the thickness of each frame.
  • the recess constitutes a gas flow path, which may be occupied by a thin, flat screen wrapped in a nonwoven fibrous material to assist in obtaining uniform gas distribution over the back of the membrane, while providing backup for the fragile membranes in the stack and having properties which promote blood coagulation so as to seal off blood flow if a pinhole leak develops in the membrane.
  • the device of the copending application offers many advantages and has gained wide-spread acceptance, but it would still be desirable to reduce the total number of parts and lineal length of the critical seals. An integral heat exchange capacity is also desirable.
  • the present invention provides a simple, industrially manufacturable membrane blood component exchanger with optimized proportions, in the sense that it is just as efficient, but of simpler construction than can be achieved with prior art designs.
  • the membrane device embodiments according to the present invention have greater biocompatibility and offer advantages in both dialysis and open-heart procedures and in partial cardiopulmonary support.
  • several embodiments of this invention provide integral heat exchange capacity. These are advantageous because almost all extracorporeal circulation procedures require heat transfer. For example, good surgical practice requires that the heat lost in the extracorporeal components be added back before the blood is returned to the body.
  • external heat exchange is used to help maintain the patient at a reduced temperature during surgical procedures.
  • an integral heat exchanger and oxygenator in which the gas exchange is by simple bubbling through the blood and the heat exchange by conventional separation of the blood from liquid coolant streams by rigid metallic walls.
  • this prior art device can cause blood trauma of the type mentioned above, and heat exchange is not efficient.
  • the deviceof the present invention is constructed primarily for use as an artificial lung, in which the carbon dioxide in the blood is supplanted with oxygen, or the device may be used asan'artificial kidney, whereupon itdialyzes blood components.
  • the description w'ill'focus on use of the device as an artificial lung for sake'of brevity.
  • the new blood component transfer device is distinguished by its simplicity and gas or liquid exchange efficiency with'low blood trauma.
  • the integral heatexchanger embodiment provides the above-mentioned additional advantages.
  • the integral device has elementary subassembly units comprising aheat exchanger close-coupled,'up Stream, or downstream, (with frame stiffening, if necessary), with one'or more blood component sub-assemblies, each of which comprises a frame having rectangular openings and'a gas permeable membrane on each face.
  • heat exchanger subassembly heat is transferred from a source or sink through a membrane into aflowing thin film of blood.
  • two confronting membranes define-a thin passageway for blood and remote sides of one or more of the membranes confront a second passageway or passageways in which 4 by virtue of its low cost; to control blood film thickness and to optimize gas diffusion; to minimize gas pressure drop; to eliminate preferential blood flow paths between membranes and from layer to layer; to minimize foreign surface areas that are in contact with blood; to eliminate sophisticated manifolding and sealing requirements, thereby reducing the probability of leaks; to seal off pinhole leaks, if any, in the membrane by clotting blood on a membrane far outside of the blood flow path; and to provide a heat exchanger for irregular surfaces with little contact resistance.
  • FIG. 1 is an exploded perspective view'of a blood heat and gas exchange assembly, including a holder and cover plate therefor;
  • FIG. 2 is an exploded perspective view of a gas exchanger sub-assembly as used in the assembly of FIG. 1, showing the optional porous support structure;
  • FIG. 3 shows the sub-assembly of FIG. 2 in which the support is in place inthe frame,,providing a depressed gas flow recess;
  • FIGS. .3A and 3B are plan and cross-sectional views,-
  • FIG. 4 is a perspective view showing one 'type of a heat exchanger tion
  • FIG. 5 is a vertical cross sectional view taken on line 55 in FIG. 4 to show a solid bottom construction in the heat exchanger sub-assembly;
  • FIG. 6 is a vertical cross-sectional view of a heat exchanger sub-assembly (conforming to line 55 in FIG. 4), but differing in construction from that of FIG. 4 in having a membrane-floating sheet combination as the bottom closure; I i
  • FIG. 7 is a perspective view showing another type of a heat exchanger sub-assembly according to this invention, this "embodimentprovidingitwo path thin film blood flow, the membranebeing partially broken away to show the internal channels;
  • FIG. 8 is a vertical cross-sectional view of the gas exchanger sub-assembly of FIG. 7 taken on line 8 -8;
  • FIG. 9- isa perspective view of a blood gas exchanger (without an integral heat exchanger) according to this invention showing a sandwich of stacked gas exchanging frames and plate and frame closure means;
  • FIG. 9 shows the blood flow path through the supported membrane envelopes.
  • FIG. I there is shown an overall layout of the lung/heat exchanger assembly 2 including a typisub-assembly according to this inven-- FIG. 10 is a cross-sectional view of the gas exchanger plate 6.
  • Cover plate 6 which may be made of metal or plastic and the like is shown ribbed for lightness and stiffness.
  • Holder 4, including mounting studs 5, can accommodate a plurality of heat exchanger/lungs on one or both sides.
  • a similar assembly 2 can be placed on the far side, but this is omitted from FIG. I
  • holder 4 For heat exchange, temperature control is provided by making holder 4 a heat source or heat sink.
  • One convenient way to do this is to provide internal channels for the passage of a heat transfer fluid, although other means, such as electrical resistance heaters and refrigerating coils can be used.
  • holder 4 is made of metal and is cored for passage of heating and cooling water through water connection ports 12 and 14. After assembly, heat will flow in either direction through the wall of holder 4, through the confronting membrane on heat exchanger subassembly 8 and into or out of the blood film.
  • oxygen or an oxygen-containing gas will enter port 16 in holder 4 and flow through gas transfer hole and seal 17, through a correspondingly aligned hole in the frame of heat exchanger 8 and thence into an aperture in oxygen exchanger l0.
  • means such as relief valve 18, can be provided to open and vent the gas before any possible damage to the lung can occur.
  • the gas then flows in a pattern more clearly understood by reference to FIG. 3 through the gas exchange sub-assembly 10, picks up carbon dioxide and the like and vents to the atmosphere through gas exhaust ports 20 and 22 and corresponding holes 24 and 26 in cover plate 6.
  • the blood then is transfered to the gas exchanger subassembly by any suitable means, such asthrough tubing or piping (not shown) but preferably by movement into close-coupled, aligned inlet port or ports in the end of sub-assembly containing the gas entrance port or ports.
  • the blood will be split into parallel flow in gas exchanger 10, then come together at one central manifold and exit lung/heat exchanger assembly 2 at blood outlet fitting 30, passing through blood outlet aperture 32 in cover plate 6. Details of the blood flow in gas exchanger 10 are seen more clearly in FIG. 3.
  • FIGS. 4-6 show in detail two constructions of heat exchanger sub-assembly 8 and illustrate single path flows.
  • These heat exchangers use the internal pressure of blood to make membrane surface 62 conform to the heat source or heat sink, e.g., the heated or cooled surface of lung holder platen 4. In this way, a highly efficient thermal junction is obtained and the adverse effect of bows, warps and waves on the surface can be conformed to and insulating air gaps avoided.
  • Membrane 62 can be made of nonporous metal or organic polymeric material, preferably an organopolysiloxane, a polycarbonate, a block copolymer of an organopolysiloxane and a polycarbonate, aluminum or stainless steel.
  • Membrane 62 (and 70, if used) is fastened to frame with a suitable adhesive or, if thermoplastic, alternatively, by heat-sealing.
  • heat exchanger 8 and gas exchanger 10 may be closely coupled in one of two ways, using a solid or a floating bottom in heat exchanger 8 to confront membrane 38 and optional distribution mat 52 in gas exchanger sub-assembly 10.
  • the heat exchanger bottom 74 is shown as a solid plastic sheet; in FIG. 6, the heat exchanger bottom closure is a floating plastic sheet 72 separating amembrane bottom of the heat exchanger from the top of gas exchanger 10.
  • a floating interface, such as is provided by the construction in FIG. 6 can move to some degree under the influence of differential pressure providing a hydraulic shim upon the gas exchanger blood envelope. This can be used to enhance the performance of the gas exchanger subassembly. It provides more uniform deflection with respect to the solid base sub-assembly of FIG. 5) to ultimately provide more uniform blood film thickness in both assemblies.
  • blood enters at inlet port 28 and spreads into a film occupying the recess under membrane 62. Passing across the recess, heat exchange can occur through the membrane, then the blood exits at ports 64 and 66.
  • FIGS. 7 and 8 An especially preferred construction of heat exchanger assembly 8 is shown in FIGS. 7 and 8.
  • Blood enters through inlet 28'into center tapered distribution channel and then flows in two thin films (e.g., 25 mils) across two active heat transfer paths under membrane 62 to either of tapered exit channels 76 and 78.
  • Such a two path flow has the advantage of permitting thinner blood films at the same overall pressure drop because of the shorter path distance and wider crosssectional areas, in comparison with the embodiment of FIG. 4. Thinner films transfer heat effectively and there is no shunt down the center as is sometimes seen in the single-path heat exchanger embodiments.
  • FIGS. 2 and 3 show in detail a construction of gas exchanger sub-assembly 10 and illustrates preferred flow paths.
  • Open gas mat insert 52 is used for advantages mentioned above.
  • the magnified view of tab 53 in FIG. 2 shows small passageways molded therein communicating with slots 55 to help distribute the gas evenly.
  • Corresponding channels can be provided at the downstream tab.
  • sub-assembly I0 is made up of one or more layers of frames 36 with membranes 38 and 40 superposed on either or both sides and the blood flows between confronting membranes.
  • oxygenating sub-assembly 10 can comprise one or more membrane envelopes interleaved with open gas mat spacers, and can comprise the thin polytetrafluoroethylene membrane envelope/gas pervious woven plastic spacer design described by Claff, et a], in above-mentioned US. Pat. No. 3,060,934.
  • the oxygenating sub-assembly can comprise one or more frames with confronting membranes and including a gas flow recess which includes an open fluid distribution element.
  • the open membrane-supportive distribution element will have a somewhat parallelogram shape to provide, with the frame margins, triangularly shaped free spaces'in communication with the blood inlet and outlet ports, into which the blood membrane envelope distends under blood pressure. This distention produces elongated blood distribution and recovery channels and facilitates transfer of the blood film smoothly across the active surface of the membrane, but only in a single path.
  • the oxygenator sub-assembly of the present invention will be of unique desigmand there will be an efficient two-pathway thin film blood flow therethrough. Increased efficiency permits either higher capacity in conventionally sized unis or the design of units with less parts than required by conventional units and equivalent oxygen transfer capability.
  • FIGS. 9 and 10 show four such frames in sandwich assemblyI
  • Each frame 36 comprises a plastic, suchas poly (vinyl chloride) or an aromatic polycarbonate, with a central open area and superposed thereon are thin gas permeable, nonporous membranes 38 and 40.
  • a suitable adhesive such as a catalyzed epoxy cement, heat sealing, or the like may be used.
  • the frame is perforated and channelled with blood inles 44 and 46 and blood outlet 48,gas inlet 50 and gas outlets 24 and 26.
  • the top membrane 38 (and bottom membrane 40) is depressable into the frame to provide a gas flow recess.
  • -frames 36 can be stacked in sandwiches, using nonporous flat cover plates 82 and 84 and spacer frames 86 on top and bottom.
  • cover plate 84 and spacer frame 86 can serve as bottom closures and the flat bottom of heat exchanger sub-assembly 8 can serve asthe top closure for the gas exchanger sub-assembly.
  • the thickness of the gas distribution element will be about 48 mils, more or less, in a mil thick frame.
  • the distribution element acts as a'support, and'blood pressure biases the blood remote surface of the membrane against the element to provide thin film free space in the blood flow envelope.
  • the three-dimensional, open gas distribution element 52 is seen to be substantially flat and to have a thickness somewhat less than the thickness of frame 36.- It is shaped like a trapezoid and togetherwith theouter margins of the frame, provides two decreasingly taperedfree spaces 54 and 56 beginning at blood inlet ports 44 and 46. Element 52 also includes centrally located increasingly tapered slot 58 which provides a corresponding free space increasingly tapered downstream and terminating at blood exit port 48. The free spaces provide elongated channels when the membrane envelope distends into-them under the influence of blood pressure.
  • the membrane For dialysis, the membrane must permit diffusion of blood impurities by liquidliquid exchange, and cellophane or other conventional dialysis membranes may be used.
  • the polycarbonate's e.g., the condensation products of his phenol-A andphosgene, block copolymers of organopolysiloxanes' and polycarbonates, polytetrafluoroethylene andth'e like.
  • the membrane For dialysis, the membrane must permit diffusion of blood impurities by liquidliquid exchange, and cellophane or other conventional dialysis membranes may be used.
  • blood component transfer sub-assembly 10 will include supportive elements 52 to back the membranes, and these can be embossed or grooved, and the like to provide multiple pathways when. the thin membrane presses against them.
  • supportive elements 52 to back the membranes, and these can be embossed or grooved, and the like to provide multiple pathways when. the thin membrane presses against them.
  • conventional membranes are smooth, they are inclined to adhere during storage and gas interchange is reduced.
  • membranes 38 and 40 are provided with thermoplastically formed protuberances 42.
  • the thickness of the membrane in the region of each protuberance is no greater than that of the smooth areas of the membrane, and the protuberances confront each other in the blood flow envelope.
  • These membranes are described for simplicity as having a cone field pattern which interdigitates, i.e., when confronting and closely coupled, the protuberances from one membrane fit into free spaces in the other.
  • the advantages of using a cone-field gas membrane to prevent membrane sticking and to provide consistent thin blood films with laminar flow and no stagnant areas are described in copending application Ser. No. 67,753, filed on Aug. 28, 1970, now U.S Pat. No. 3,724,673 by one of the present appplicants and incorporated herein by reference to avoid lengthy repetition.
  • the textured surface is created by heating, vacuum forming and cooling on a suitable die.
  • An ideal material for the membranes in sub-assembly is an organopolysiloxane-polycarbonate block copolymer whose composition is described in US. Pat. No. 3,189,662 which is assigned to General Electric Company, the assignee of this application.
  • a membrane of this type is designated by that company as ME- M-213.
  • ME- M-213 In a device of the type disclosed herein, such a membrane has a high transfer coefficient for carbon dioxide and removes carbon dioxide approximately at the rate of 80 percent of the rate of oxygen addition. This approximates the rate of gas transfer in the human lung. The transfer coefficient of this material for oxygen is also comparatively high.
  • a membrane made of the above-mentioned material also has the desirable property of not tearing catastrophically when it is punctured as do some of the weaker silicone membranes which have previously been used in blood oxygenators.
  • heat exchanger/lung 2 which lie between holder 4 and plate 6 in FIG. 1 are assembled in the factory as a package. This is installed in the holder-plate combination which clamps the package to preclude blood and gas leaks and which provides oxygen and blood inlet and outlet connections.
  • a single assembly package such as shown in FIG. 1, and having 4 gas exchanger frames is about /sth inch thick when stacked and compressed.
  • a gas-exchanger of 4 frames thickness with cover plates (FIG. 9) is a little more than firth inch thick when stacked and compressed. In either case using the dimensions given above, an oxygenator of this type provides enough gas exchange area for localized perfusion of an organ.
  • each gas exchanger e.g. 12 instead of 1-4
  • blood handling capacity can be attained for perfusing the whole body of an infant or an adult without fear of building up such internal pressure as to cause rupture of the membranes. Blood pressure and gas pressure drops in the oxygenator are acceptably low.
  • Typical performance characteristics of a 11 /2 X 24 inch unit show that gas transfer performance characteristics are uniformly high (60 ml. O lmin. M and 40 ml. Co /min. M Heat transfer resuls are superior.
  • the overall heat transfer coefficients were 142 Btu/hr. ft F. with a 1 mil aluminum membrane, 1 17 Btu/hr. ft F. with a 2 mil organopolysiloxanepolycarbonate block copolymer membrane, and 104 Btu/hr. ft F. with a 3 mil polycarbonate membrane.
  • a 1.5 mil stainless steel membrane or a 2 mil polycarbonate membrane provide equally efficient heat transfer.
  • ponent transfer device comprising a. a heat exchanger sub-assembly including i. a substantially planar frame having an open central area closed at the bottom with a thin membrane in combination with a floating sheet-like element disposed within the frame opening,
  • each blood component exchanger frame in open communication with said central area
  • each blood component exchanger frame iv. thin membranes superposed respectively on the top and the bottom surfaces of each blood component exchanger frame and forming with said blood inlet and outlet means a blood flow envelope, the blood remote surface of one or both said membranes constituting the top or bottom of a depressable fluid flow recess in each blood component exchanger frame,
  • fluid outlet means at the other end of each blood component exchanger frame in open communication with said fluid flow recess, when depressed
  • closure means superposed on one or both surfaces of each blood component exchanger frame to define with the blood remote surface or surfaces of said membrane or membranes, the fluid inlet means, and the fluid outlet means, a blood component exchange fluid flow chamber, the blood remote surface of one or both said membranes constituting the top or bottom of said chamber and viii. a fluid distribution element in at least one said fluid flow chamber, said element being substantially flat, membrane-supportive and open to the passage of fluid and c. means to transfer the blood between said exchangers.
  • a device as defined in claim 1 wherein the means to transfer the blood comprises a stacked assembly consisting of the heat exchanger and the blood component exchanger, the blood outlet from one exchanger being aligned and close-coupled with the blood inlet to the other exchanger.
  • a device as defined in claim 1 wherein the thin membrane adhered to the top surface of the heatex changer frame is comprised of metal or an organic polymeric material.
  • a device as defined in claim 3 wherein said membrane comprises an organopolysiloxane, a polycarbonate, a block copolymer of an organopolysiloxane and a polycarbonate, aluminum or stainless steel.
  • each blood component exchanger frame has a myriad of protuberances permanently formed in them in which the thickness of the membrane in the region of each protuberance is no greater than that of the smooth areas of the membrane, and the protuberances confront each other in said blood flow envelope.
  • each said blood component exchanger frame comprise an organopolysiloxane, a
  • polycarbonate or a block copolymer of an organopolysiloxane and a polycarbonate.
  • each said fluid distribution element includes fluid flow channels means, a blood component exchange gas flow-chamber and a gas distribution element.
  • each said gas distribution element includes gas flow channels on is opposed'major planar surfaces.
  • a device as defined in claim 1 including a plurality of blood component exchanger frames, blood flow envelopes, fluid flow recesses'and fluid distribution elements, in stacked assembly.
  • a membrane type blood heat and gas exchange device comprising a. a heat exchanger sub-assembly including i. a plate with a central recess open at the top, ii. a blood inlet port centrally located at one'end of said plate in open communication with said recess and terminating in a decreasingly tapered longitudinal entrance channel centrally located in the bottom of said recess,
  • a blood gas exchanger sub-assembly including i. at least one substantially planarframe having a central open area,
  • each blood gas exchanger frame having a myriad ,of protuberances permanently formed in them in which the thickness of the membrane in the region of each protuberance is no greater than that of the smooth areas of the membranes, said membranes being superposed respectively on the top and bottom. surfaces of each blood gas exchanger frame, the protuberances confronting each other, the membranes forming with the blood inlet and outlet ports a blood flow envelope, the blood remote surface of each membrane constituting the bottom or top of a depressable gas flow recess in each blood gas exchanger frame,
  • each blood gas exchanger frame in' open communication with said gas flow recess, when depressed
  • a gas distribution element on the blood remote surface of each said membrane said element being substantially flat, 'membrane-supportive, including gas flow channels on-its opposed major planar surfaces and having a thickness somewhat less than the frame thickness, and being shaped like a trapezoid to provide with the outer margins of each said.
  • closure means comprising the bottom of said heat exchanger superposed-on the top surface of the uppermost said element, depressing said element and the top membrane of the gas exchanger into the recess of the uppermost gas exchanger frame to'define with the blood remote surface of said membrane, the gas inlet' port, and the gas outlet ports a blood gas flow chamber whose depth is equal'to the element thickness and to compress said blood flow envelope to provide a relatively thin film space between the confronting membranes, the heat exchanger and the gas exchanger being in stacked relationship, the blood outlet ports of the heat exchanger being aligned and close-coupled with the. blood inlet ports of the gas exchanger.
  • the thin membrane superposed on the top surface of theheat exchanger plate is comprised of a metal or an organic polymeric material.
  • a device as defined in claim 14 wherein the membrane comprises stainless steel or a polycarbonate.
  • each said gas exchanger frame comprise an organopolysiloxane, a polycarbonate or a block copolymer of an organopolysiloxane and a polycarbonate.
  • bottom closure means comprising a plate and spacer superposed on the bottom surfaceof the lowermost said element, depressing said element and the bottom member of the gas exchanger into the bottommost gas exchanger frame to provide a corresponding blood gas flow chamber.
  • a device as defined in claim 13 including a plurality of blood gas exchanger frames, blood flow envelopes, gas flow recesses and gas distribution elements, in stacked assembly.
  • a two flow path, membrane blood gas exchanger comprising i. at least one substantially planar frame having a central open area,
  • thin membranes having a myriad of protuberances permanently formed in them in which the thickness of the membrane in the region of each protuberance is no greater than that of the smooth areas of the membranes, said membranes being superposed respectively on the top and bottom surfaces of each blood gas exchanger frame, the protuberances confronting each other, the membranes forming with the blood inlet and outlet ports a blood flow envelope, the blood remote surface of each membrane constituting the bottom or top of a depressable gas flow recess in each frame,
  • a gas distribution element on the blood remote surface of each said membrane said element being substantially flat, membrane-supportive and open to gas flow and having a thickness somewhat less than the frame thickness, and being shaped like a trapezoid to provide with the outer margins of each said frame two decreasingly tapered channels which begin at the blood inlet ports and including a centrally located increasingly tapered channel terminating at the blood exit port, said channels providing free spaces into which the membrane envelope can distend with limits to effect a pair of elongated blood channels beginning at the blood entrance ports and an elongated blood channel beginning within the gas exchanger and terminating at the blood exit port, when the space between the membranes is under blood pressure, whereby the blood is passed across the gas exchange membrane in two thin film pathways, and
  • closure means comprising a plate and spacer superposed on the top surface of the uppermost said element, depressing said element and the top membrane of the gas exchanger into the recess of the uppermost gas exchanger frame to define with the blood remote surface of said membrane, the gas inlet port, and the gas outlet ports a blood gas flow chamber whose depth is equal to the element thickness and to compress said blood flow envelope to provide a relatively thin film space between the confronting membranes.
  • bottom closure means comprising a plate and spacer superposed on the bottom surface of the lowermost said ele-
  • a device as defined in claim 20 including a plurality of blood gas exchanger frames, blood flow envelopes, gas flow recesses and gas distribution elements,

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  • Chemical & Material Sciences (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Health & Medical Sciences (AREA)
  • Urology & Nephrology (AREA)
  • Engineering & Computer Science (AREA)
  • Water Supply & Treatment (AREA)
  • External Artificial Organs (AREA)
US00247987A 1972-04-27 1972-04-27 Integral blood heat and component exchange device and two flow path membrane blood gas exchanger Expired - Lifetime US3839204A (en)

Priority Applications (7)

Application Number Priority Date Filing Date Title
US00247987A US3839204A (en) 1972-04-27 1972-04-27 Integral blood heat and component exchange device and two flow path membrane blood gas exchanger
CA159,496A CA1002844A (en) 1972-04-27 1972-12-20 Integral blood heat and component exchange device and two flow path membrane blood gas exchanger
SE7305569A SE405681B (sv) 1972-04-27 1973-04-18 Blodvermevexlar- och blodkomponentoverforingsanordning
JP48046275A JPS4942188A (de) 1972-04-27 1973-04-25
DE2321131A DE2321131A1 (de) 1972-04-27 1973-04-26 Integrales geraet zum austausch von blutwaerme und blutbestandteilen
GB265776A GB1437634A (en) 1972-04-27 1973-04-27 Blood heat and component exchange device
GB2004573A GB1437633A (en) 1972-04-27 1973-04-27 Blood heat and component exchange device

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US00247987A US3839204A (en) 1972-04-27 1972-04-27 Integral blood heat and component exchange device and two flow path membrane blood gas exchanger

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JP (1) JPS4942188A (de)
CA (1) CA1002844A (de)
DE (1) DE2321131A1 (de)
GB (2) GB1437633A (de)
SE (1) SE405681B (de)

Cited By (29)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4146480A (en) * 1976-08-19 1979-03-27 Chirana, Koncern Hemicapillar plate dialyzer
US4168293A (en) * 1977-03-07 1979-09-18 Bramson Mogens L Blood oxygenator
US4256692A (en) * 1979-02-01 1981-03-17 C. R. Bard, Inc. Membrane oxygenator
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US8808541B2 (en) 2008-03-03 2014-08-19 Marwan Nasralla Dialysis cell and tray for dialysis cells
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US9595206B2 (en) 2008-02-11 2017-03-14 The General Hospital System and method for in vitro blood vessel modeling
DE102016009534A1 (de) * 2016-08-08 2018-02-08 Xenios Ag Oxygenator mit einer Gehäusewandung
CN117504026A (zh) * 2023-12-25 2024-02-06 天津大学 用于体外膜肺氧合的氧合器组件

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CH623746A5 (en) * 1977-03-21 1981-06-30 American Hospital Supply Corp Mass transfer apparatus with a semipermeable membrane
SE7801230L (sv) * 1978-02-02 1979-08-03 Gambro Ab Anordning for diffusion av emnen mellan tva fluida under samtidig temperering av atminstone det ena av dessa fluider
FR2478482A1 (fr) * 1980-03-21 1981-09-25 Lidorenko Nikolai Membrane permeable aux gaz, procede de fabrication de celle-ci et oxygenateur de sang utilisant ladite membrane
CN115518219B (zh) * 2022-08-30 2023-06-16 四川大学华西医院 一种低容量活化白细胞吸附器

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US4146480A (en) * 1976-08-19 1979-03-27 Chirana, Koncern Hemicapillar plate dialyzer
US4168293A (en) * 1977-03-07 1979-09-18 Bramson Mogens L Blood oxygenator
US4308230A (en) * 1977-03-07 1981-12-29 Bramson Mogens L Blood oxygenator
US4411872A (en) * 1977-03-07 1983-10-25 Bramson Mogens L Water unit for use with a membrane blood oxygenator
US4256692A (en) * 1979-02-01 1981-03-17 C. R. Bard, Inc. Membrane oxygenator
US4490331A (en) * 1982-02-12 1984-12-25 Steg Jr Robert F Extracorporeal blood processing system
US4599093A (en) * 1982-02-12 1986-07-08 Steg Jr Robert F Extracorporeal blood processing system
US4556489A (en) * 1983-03-09 1985-12-03 Shiley Incorporated Membrane oxygenator
US4735775A (en) * 1984-02-27 1988-04-05 Baxter Travenol Laboratories, Inc. Mass transfer device having a heat-exchanger
US5589389A (en) * 1991-07-03 1996-12-31 Fondation Nationale De Transfusion Sanguine Apparatus for causing medicinal products to penetrate into red blood cells
US5939023A (en) * 1993-01-19 1999-08-17 Thermogenesis Corp. Fibrinogen processing apparatus method and container
US5656501A (en) * 1993-08-11 1997-08-12 Yissum Research Development Company Of The Hebrew University Of Jerusalem Flow cell device for monitoring blood or other cell suspension under flow
EP0901405B1 (de) * 1996-05-24 2003-12-03 Thermogenesis Corporation Fibrinogen-apparat, methode und behälter
US6077447A (en) * 1996-05-24 2000-06-20 Thermogenesis Corp. Fibrinogen apparatus, method and container
EP0901405A1 (de) * 1996-05-24 1999-03-17 Thermogenesis Corporation Fibrinogen-apparat, methode und behälter
US6241945B1 (en) * 1998-03-16 2001-06-05 Life Science Holdings, Inc. Modular combined pump, filtration, oxygenation and/or debubbler apparatus
US6117390A (en) * 1998-03-27 2000-09-12 Medtronic, Inc. Compact blood oxygenator utilizing longitudinally interspersed transversely extending heat exchanger conduits and oxygenator fibers
US7759113B2 (en) 1999-04-30 2010-07-20 The General Hospital Corporation Fabrication of tissue lamina using microfabricated two-dimensional molds
US8642336B2 (en) 1999-04-30 2014-02-04 The General Hospital Corporation Fabrication of vascularized tissue using microfabricated two-dimensional molds
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US20100098742A1 (en) * 1999-04-30 2010-04-22 Vacanti Joseph P Fabrication of tissue lamina using microfabricated two-dimensional molds
US20050202557A1 (en) * 2000-04-28 2005-09-15 Jeffrey Borenstein Micromachined bilayer unit of engineered tissues
US7776021B2 (en) 2000-04-28 2010-08-17 The Charles Stark Draper Laboratory Micromachined bilayer unit for filtration of small molecules
US9738860B2 (en) 2000-04-28 2017-08-22 The General Hospital Corporation Fabrication of vascularized tissue using microfabricated two-dimensional molds
US8491561B2 (en) 2002-03-25 2013-07-23 The Charles Stark Draper Laboratory Micromachined bilayer unit of engineered tissues
US8147562B2 (en) 2002-09-23 2012-04-03 The General Hospital Corporation Three dimensional construct for the design and fabrication of physiological fluidic networks
US20060136182A1 (en) * 2002-09-23 2006-06-22 Vacanti Joseph P Three dimensional construct for the design and fabrication of physiological fluidic networks
US20060019326A1 (en) * 2003-01-16 2006-01-26 Vacanti Joseph P Use of three-dimensional microfabricated tissue engineered systems for pharmacologic applications
US7670797B2 (en) 2003-01-16 2010-03-02 The General Hospital Corporation Method of determining toxicity with three dimensional structures
US8173361B2 (en) 2003-01-16 2012-05-08 The General Hospital Corporation Method of determining metabolism of a test agent
US20070281353A1 (en) * 2003-05-21 2007-12-06 Vacanti Joseph P Microfabricated Compositions and Processes for Engineering Tissues Containing Multiple Cell Types
US8357528B2 (en) 2003-05-21 2013-01-22 The General Hospital Corporation Microfabricated compositions and processes for engineering tissues containing multiple cell types
US7960166B2 (en) 2003-05-21 2011-06-14 The General Hospital Corporation Microfabricated compositions and processes for engineering tissues containing multiple cell types
US8865466B2 (en) 2003-08-18 2014-10-21 The Charles Stark Draper Laboratory Nanotopographic compositions and methods for cellular organization in tissue engineered structures
US8097456B2 (en) 2003-08-18 2012-01-17 The Charles Stark Draper Laboratory Nanotopographic compositions and methods for cellular organization in tissue engineered structures
US20080026464A1 (en) * 2003-08-18 2008-01-31 Borenstein Jeffrey T Nanotopographic Compositions and Methods for Cellular Organization in Tissue Engineered Structures
US20100252528A1 (en) * 2006-07-03 2010-10-07 Fuji Xerox Co., Ltd. Liquid droplet ejection head, apparatus for ejecting liquid droplet, and method of producing liquid droplet ejection head
US8176630B2 (en) * 2006-07-03 2012-05-15 Fuji Xerox Co., Ltd. Method of producing liquid droplet ejection head
US10939989B2 (en) 2007-04-12 2021-03-09 The General Hospital Corporation Biomimetic vascular network and devices using the same
US8951302B2 (en) 2007-04-12 2015-02-10 The General Hospital Corporation Biomimetic vascular network and devices using the same
US9498320B2 (en) 2007-04-12 2016-11-22 The General Hospital Corporation Biomimetic vascular network and devices using the same
US20100234678A1 (en) * 2007-04-12 2010-09-16 The General Hospital Corporation Biomimetic vascular network and devices using the same
US20100274353A1 (en) * 2007-04-12 2010-10-28 The General Hospital Corporation Biomimetic vascular network and devices using the same
US8591597B2 (en) 2007-04-12 2013-11-26 The General Hospital Corporation Biomimetic vascular network and devices using the same
US10265698B2 (en) 2007-09-19 2019-04-23 The Charles Stark Draper Laboratory, Inc. Microfluidic structures for biomedical applications
US20090181200A1 (en) * 2007-09-19 2009-07-16 Borenstein Jeffrey T Microfluidic Structures for Biomedical Applications
US8266791B2 (en) * 2007-09-19 2012-09-18 The Charles Stark Draper Laboratory, Inc. Method of fabricating microfluidic structures for biomedical applications
US20130004386A1 (en) * 2007-09-19 2013-01-03 Borenstein Jeffrey T Fabricating microfluidic structures for biomedical applications
US9181082B2 (en) * 2007-09-19 2015-11-10 The Charles Stark Draper Laboratory, Inc. microfluidic structures for biomedical applications
US9595206B2 (en) 2008-02-11 2017-03-14 The General Hospital System and method for in vitro blood vessel modeling
US8808541B2 (en) 2008-03-03 2014-08-19 Marwan Nasralla Dialysis cell and tray for dialysis cells
US20150136371A1 (en) * 2012-06-04 2015-05-21 Alfa Laval Corporate Ab End-piece & plate heat exchanger comprising, and method of making, such end-piece
US11231240B2 (en) * 2012-06-04 2022-01-25 Alfa Laval Corporate Ab End-piece and plate heat exchanger comprising, and method of making, such end-piece
US11709025B2 (en) 2012-06-04 2023-07-25 Alfa Laval Corporate Ab End-piece and plate heat exchanger comprising, and method of making, such end-piece
DE102016009534A1 (de) * 2016-08-08 2018-02-08 Xenios Ag Oxygenator mit einer Gehäusewandung
CN117504026B (zh) * 2023-12-25 2024-05-07 天津大学 用于体外膜肺氧合的氧合器组件
CN117504026A (zh) * 2023-12-25 2024-02-06 天津大学 用于体外膜肺氧合的氧合器组件

Also Published As

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JPS4942188A (de) 1974-04-20
CA1002844A (en) 1977-01-04
SE405681B (sv) 1978-12-27
DE2321131A1 (de) 1973-10-31
GB1437634A (en) 1976-06-03
GB1437633A (en) 1976-06-03

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